Bioartificial implants and methods for their manufacture and use are described, particularly bioartificial pancreases. In particular, the implants may be thin sheets which enclose cells, may be completely biocompatible over extended periods of time and may not induce fibrosis. The high-density-cell-containing thin sheets are preferably completely retrievable, and have dimensions allowing maintenance of optimal tissue viability through rapid diffusion of nutrients and oxygen and also allowing rapid changes in the secretion rate of insulin and/or other bioactive agents in response to changing physiology. Implantations of living cells, tissue, drugs, medicines and/or enzymes, contained in the bioartificial implants may be made to treat and/or prevent disease.

1. Field of the Invention
The present invention is directed to the field of bioartificial pancreases, bioartificial implants generally, and methods for their manufacture and use. In particular, the present invention is directed to the fabrication of thin sheets which enclose cells, which are completely biocompatible over extended periods of time and which do not induce fibrosis. The present invention also concerns cell-containing thin sheets which are easily completely retrievable, and which have dimensions allowing maintenance of optimal tissue viability through rapid diffusion of nutrients and oxygen and also allowing rapid changes in the secretion rate of insulin and/or other bioactive agents in response to changing physiology. The present invention also concerns implantations made using these bioartificial implants. The present invention may be used for implantation of living cells, tissue, drugs, medicines and/or enzymes, contained in the bioartificial implants.
2. Discussion of the Background
Traditional medical treatments for functional deficiencies of biological organs have focused on replacing identified normal secreted products of the deficient organ with natural or synthetic pharmaceutical compositions. For example, for treating insulin-dependent diabetes mellitus (IDDM), also known as type I or juvenile diabetes, the normal secretion of insulin by the islets of Langerhans of the pancreas must be replaced since functional islets are no longer present in the pancreas. This islet function is emulated by administering insulin, titrating the injections in response to blood glucose level measurements. The normal production of hormone by the islets is poorly approximated. This therapy is known to be associated with premature morbidity and mortality.
Organ replacement has also been applied. For IDDM, whole pancreas and islet transplants both have been performed with significant success1. Such transplants require continuous use of immunosuppressive agents to prevent immunological rejection of the organ, depriving the patient of the full protective function of the immune system against disease and subjecting the patient to the side effects of the drugs.
The bioartificial implant is the manufactured solution to replacing organ function without reliance on immune suppression; this topic has been reviewed2,3,4,5,6. Many approaches have been tried for fabrication of bioartificial implants having in common the use of some semipermeable barrier allowing the tissue to function and simultaneously protecting tissue from rejection. Prior to the present invention, such bioartificial implants have proven unsatisfactory for a variety of reasons.
Because of severe limits on availability of human tissue, a practical therapy for IDDM will likely require the use of xenografts, most likely of porcine tissue. Porcine tissue is known to stimulate a vigorous immune response in humans, including complement mediated rejection of the xenograft, posing a significant obstacle to use of porcine tissue in a bioartificial implant. The bioartificial implant barrier should sufficiently exclude antibody-complement to prevent complement mediated damage to cell and tissue xenografts.
Some bioartificial implants require grafting into the vascular system, usually with connections to an artery and a vein to take advantage of the pressure difference. Blood flow through such vascular grafts has proven to be traumatic to blood, and continuous systemic administration of pharmaceutical preparations to prevent clotting and foreign body reactions is required. Thus optimal bioartificial implant design, not requiring continuous systemic pharmaceutical administration, is limited to implants that rely on passive diffusion.
Most such passive diffusion bioartificial implants fail because their dimensions are such that the enclosed tissues cannot receive enough nutrients, especially oxygen. When tissue is starved of oxygen its metabolism declines and it loses its ability to secrete hormone. Extended hypoxia leads to cell death.
In these same devices, the tissue may be prevented from responding in a timely way to changes in the physiological environment because of the dimensions of the bioartificial implant. In the case of implants containing insulin-producing islets, an unsatisfactory bioartificial implant may not be able to sense that previously secreted insulin has successfully reduced blood sugar levels, and thus, will continue to secrete insulin even when the effect of this insulin is to plunge blood sugar levels below normal, endangering the host.
Many bioartificial implants fail because their surface is not biocompatible. When exposed to living tissues, especially when they have been seeded with allogeneic or xenogeneic living tissue, they provoke a foreign body response. The foreign body response may be caused by a material on the surface of the implant, antigens shed by the cells within, or by a combination of both. The foreign body response includes fibrosis, in which fibroblasts and macrophages apply proteins including collagen to the surface of the implant, attracting other effector cells, and eventually leading to the formation of a capsule of connective tissue that isolates and starves the implant.
Some bioartificial implants are unsatisfactory because they cannot be easily removed in the event of implant failure or dysfunction.
Some processes previously developed for fabrication of bioartificial implants did not yield reproducible products having the desired porosity and thickness required for the implant.
Some processes previously developed did not completely cover the living tissue, thus allowing access by host immune system to the living tissue, leading to foreign body reactions and/or sensitization and antibody formation followed by complement-mediated lysis.
Some processes previously developed for bioartificial pancreas implants did not make efficient use of islets, wasting a significant fraction of them during fabrication.
Some bioartificial implants are so bulky that implantation is difficult or impossible. This problem occurs when only a small fraction of the volume of the implant consists of living cells.
Prior to the present invention, all bioartificial implants have proven unsatisfactory for one or more of these reasons, and for other reasons as well.
The need for complete retrieval of the bioartificial implant in the event of failure has been stressed by several workers in the field7,8,9, especially Paul Lacy, a recognized leader in islet implant research. He has criticized encapsulated islets9:
xe2x80x9cTo be feasible for broad use, the capsules would have to be smaller and more stable. In addition, investigators would have to develop a way to retrieve all the capsules readily in the event removal became necessary.xe2x80x9d
Another reason that the optimal bioartificial implant must be easily completely retrievable is that such devices will require review by the FDA""s division of biologics before sales in the United States10. Such review examines all safety issues and risks, including ease of retrieval in the event removal becomes necessary. A clinical trial of a bioartificial implant in the United States was done under an FDA approved protocol11.
It is now widely recognized that a successful bioartificial implant must have dimensions that permit efficient diffusion of nutrients into the implant and secretion of bioactive agents out of the implant. Yet the vast majority of bioartificial implants described in the literature have dimensions which make efficient diffusion impossible, either because they were manufactured before the magnitude of the requirement was understood, or because there was no art to manufature the implant with the required dimentions.
Theoretical studies have predicted the maximum dimensions permissible based on the physics of diffusion. The maximum dimension is a function of the density of tissue in the implant. Experimental studies confirm the theoretical limits to passive diffusion and point to the parameters of implant dimension.
Diffusion both into and out of the bioartificial implant must be considered. Secreted products must diffuse out of the bioartificial implant efficiently. Nutrients must diffuse in at a rate sufficient to support normal cellular metabolism. The rate-limiting nutrient is oxygen, and implants that die from lack of nutrients usually die of hypoxia.
First, in an islet bioartificial implant, insulin must diffuse quickly out of the device in response to changes in ambient glucose levels. Implants that are too large delay insulin response. For instance, after glucose stimulus is removed, hollow fiber implants (730 xcexcm O.D.) continue to secrete insulin long after glucose has normalized12. This excess insulin can result in potentially life-threatening low blood sugar.
Experimental studies have shown that bioartificial implants that are larger than 350 xcexcm in their shortest dimension significantly delay the release of insulin in response to glucose challenge13,14. Although studies of insulin release kinetics in vitro alone are useful, glucose tolerance and insulin levels should be measured in vivo in an animal model to more conclusively determine the potential effectiveness of a particular implant structure and design.
Second, the most difficult problem associated with implants relying on passive diffusion is oxygen diffusion. The importance of oxygen diffusion has only been recognized relatively recently. Current theoretical models predict that oxygen diffuses to a depth of less than 200 xcexcm through living tissue5,15. The most detailed analysis of the relationship between implant dimensions, implant shape, engraftment, oxygen tension and islet viability has been published recently by Colton5:
Maintenance of maximum cell viability and function is essential and, in the absence of immune rejection, is limited by the supply of nutrients and oxygen, especially the latter . . . The oxygen levels to which the islet cells are exposed are important from two standpoints, viability and function . . . Planar diffusion chambers, preferably with high tissue density, represent an attractive configuration for immunoisolation devices. Diffusion chambers prepared with parallel, flat sheet microporous membranes were employed extensively several decades ago in early studies of immune rejection during transplantation. Invariably, the membranes employed produced an extensive fibrotic foreign body response composed of an avascular layer of fibroblasts in a collagen matrix which restricted the supply of oxygen and nutrients, resulting in minimal survival of the encapsulated tissue . . . Only when the oxygen source is brought to within about 25 xcexcm from the surface of the transplanted tissue does the pO2 at the center of a 100 xcexcm-thick slab stay above zero.
This analysis shows that diffusion of oxygen is crucial for islet viability and function and that the shortest dimension of the coating, capsule or slab/sheet permitting oxygen diffusion throughout the structure ranges up from 100 xcexcm depending on tissue density, implant configuration and the proximity of oxygenated tissue.
Studies of islets in hollow fibers, microcapsules and coatings have supported these theoretical conclusions14,16,17,18. NMR/EPR studies of O2 concentration suggest that oxygen is low in alginate capsules19. These observations confirm that the configuration of the device must be very thin. As a rule of thumb, each cell must be less than 200 xcexcm from the surface of the bioartificial implant to receive oxygen, assuming that the implant is in contact with well oxygenated tissue.
There is considerable confusion about the term xe2x80x9cbiocompatibility.xe2x80x9d The sciences concerned with implantable medical devices use the term very differently from the sciences concerned with implants. For a device, biocompatibility means that the material induces engraftment, e.g., the vascular graft is covered with a layer of collagen fibers. This permits overgrowth of endothelial cells, which is desirable for a vascular graft. In contrast, such overgrowth will starve a cellular implant. Thus, biocompatibility for a living implant means the material will not promote cellular adhesion. The term xe2x80x9cbiocompatiblexe2x80x9d is used here to mean that the material by itself or in combination with living tissues does not produce foreign body reaction or fibrosis.
Surprisingly few materials meet this definition. It is generally believed that, the foreign body reaction is initiated when proteins adhere to the foreign body20. Thus the material, to prevent the initial step of protein adsorption, should be very hydrophilic. For example, almost every biocompatible polymer is a polysaccharide, a polyalcohol, an organic acid, or a combination thereof.
Most published work makes use of alginate, a polymer of alginic acids, which are sugar acids. Other biomaterials that are claimed to be biocompatible include agarose21, agarose/poly(styrene sulfonic acid)22, hydroxyethyl methacrylate-methyl methacrylate copolymer23, polyvinyl alcohol24,25, protamine-heparin26 and others. One group has photopolymerized a skin of polyethylene glycol onto alginate to improve its biocompatibility20; another used free radical polymerization of ethylene oxide and alginate to improve stability27.
The most commonly used material for fabrication of bioartificial implants has been alginate, usually in combination with a polycation such as poly-L-lysine to form a membrane. The original alginate/polylysine capsule was shown to ameliorate diabetes in mice over fifteen years ago28.
This occurrence of alginate in nature is mainly in the marine brown algae (Phaeophyta), soil bacteria and Pseudomonas. Alginate is a family of unbranched co-polymers of (1-4)-linked xcex2-D-mannuronic acid (M) and xcex1-L-guluronic acid (G). It is located in the intercellular algae matrix as a gel containing cations (predominantly Ca2+) that crosslink the polymer fibers. Alginates appear to be block co-polymers comprised of homopolymeric blocks of M and G with regions of alternating MG. Methods have been developed for purification of high M and high G fractions of various molecular weights29,30,31,32 sufficiently pure to make them biocompatible33,34,35,36.
Alginates obtained from marine algae comprise approximately 40% of the dry weight of the kelp. Because of its ability to retain water and its gelling, viscosifying and stabilizing properties, alginate is widely used industrially.
Until recently, alginate/polylysine capsules induced fibrosis and were not biocompatible3. Grafts failed over periods of days and months. Such grafts were found to be covered with dense fibrous overgrowth.
These capsules caused fibrosis for several possible reasons. First, polylysine is fibrogenic. Capsules made with alginate alone are less fibrogenic37. In addition, researchers at the University of Giexcex2en and the University of Wxc3xcrzburg36,35, and separately at the University of California33,34,29, succeeded in showing that alginate fibrosis was caused by impurities in alginate. Sufficiently purified alginate does not induce fibrosis. (The concept proposed by University of Trondheim that high-guluronate alginates are biocompatible while high-mannuronate are not38 has been shown to be incorrect37,39.) Thus, alginate can be made biocompatible (as defined above) with a series of rigorous purification steps.
One of the present inventors (Dorian) in collaboration with researchers at the University of California established that removal of sufficient contaminants from alginates results in alginate fractions that are nonfibrogenic, regardless of the G, M and GM content33,34. It was also shown that the molecular weight and block contents can be manipulated to produce alginates with desirable physical properties. Thus, it is now possible to produce both high M and high G alginates that are biocompatible with and without cells or islets.
Finally, it is worth noting that some workers in the field have concluded that biocompatibility, as we have defined it, is not necessary for a successful implant. Instead of a material that is ignored by the body""s foreign body reaction cells, they seek one that produces a certain type of foreign body reaction2:
Biocompatibility is most often achieved by a careful manipulation of composition, purity, geometry, handling, surface morphology, and surgical techniques to yield and implant and implant site which is sufficiently inoffensive to the host to remain below the threshold of stimulation required to provoke macrophage activation and fibroblast deposition . . . Less frequently but also successfully, biocompatibility can be obtained by texturing the surface of the implant to encourage the growth of a host vascular network at the implant surface . . . This strategy no longer requires membrane and materials which to not engender a foreign body response and consequently permits somewhat greater latitude in setting membrane transport requirements . . . This approach has been tried in the past without success, and was patented40.
We reject this approach because we believe that strict neutrality is desirable. For us, xe2x80x9cbiocompatiblexe2x80x9d means that the material by itself or in combination with living tissues does not produce foreign body reaction or fibrosis.
Pancreatic islet cells in vivo receive arterial blood, and therefore, sense the same levels of nutrients and hormones in the blood prevalent elsewhere in the body. Islet cells in a bioartificial implant may experience higher levels of their own secreted hormones because they are dependent on diffusion to is disperse hormones. A bioartificial implant which inhibits or impedes diffusion of hormones will cause islet cells to respond to an artificially high concentration of hormones. For example, secretion of insulin by islets is inhibited by high ambient levels of insulin41. It may be advantageous to make the implant as thin as possible and thus aid the diffusion process.
As described previously, passive diffusion of nutrients, oxygen and secretory products such as insulin (M.W.=7 kD) should be uninhibited to maximize the effectiveness of a bioartificial implant. This suggests that the membrane or coat of the bioartificial implant should have large pores. Larger pores, however, would admit antibodies (M.W.=160 kD), and larger, if sufficiently, complement (M.W. [Clq]=390 kD). If antibody and complement can penetrate the coat or membrane, the cells inside the implant are at risk of lysis and death.
Microcapsules have been made that inhibit antibody and complement diffusion sufficient to prevent islet lysis and permit normalization of blood sugar in mice. This was shown even when immune sensitization was demonstrated using MLC cultures36. However, similar results in higher mammals have not been reported.
The complement system, which exists in its most active (xe2x80x9ccompletexe2x80x9d) form only in higher mammals, is triggered by antibody and can kill foreign tissue in minutes42. Normally, allografts unprotected by bioartificial barriers are killed by cellular attack, not complement attack. However, xenografts often trigger a vigorous antibody and complement response. In some donor-recipient combinations (e.g., pig-to-dog), preformed antibodies exist and the complement response occurs minutes after implantation, before sensitization can occur.
The vast majority of islet implant studies have been performed using inbred mouse strains as recipients. These animals are deficient at mounting a complement mediated response, and such studies are thus not predictive of, for example, a human response to xenografts43.
Because of ethical concerns and a shortage of suitable human tissue, one practical therapy for human diabetes is a xenograft bioartificial implant. Recent studies, however, have demonstrated that porcine-to-monkey xenografts can trigger a vigorous antibody and complement response, raising grave concerns for porcine-to-human xenografts44.
The optimal bioartificial implant should prevent diffusion of antibody and complement sufficiently well to prevent antibody and complement lysis of the living cells within the bioartificial implant. Microporous membranes by their nature do not have a sharp molecular weight cutoff. Rather, the membranes increasingly inhibit diffusion as molecular weight increases, in a manner represented by a sigmoid curve5. Thus, free diffusion of insulin and sufficient inhibition of complement diffusion require a subtle and complex xe2x80x9ctuningxe2x80x9d of the membrane. Experimental demonstration of this phenomenon caused the Giexcex2en group to comment45:
xe2x80x9cOur results lead to the concept of persistent immune interaction after xe2x80x98immunoisolatedxe2x80x99 transplantation. In this case a bioartificial pancreas could not be described as an immunoisolated islet transplantation but as an xe2x80x98artificially immunoprivileged site of transplantation.xe2x80x99xe2x80x9d
In conclusion, the concept of immunoisolation should be supplanted by a recognition that the ideal implant is a subtle balance of multiple demands, including the molecular weight diffusion function of the membrane or coat, in one strategy to fabricate a successful bioartificial implant.
Islets are precious. A loss of fifty percent of the islets during fabrication of the bioartificial implant would mean only half as many people with IDDM could be implanted. Some technologies are known to have a poor yield. For instance, air knife coating has a yield of 70%46, and barium alginate density gradient coating has a yield of 40%47. Most published methods do not report the yield, or survival rate, of islets.
Another form of inefficiency is a device design that includes too much xe2x80x9cdeadxe2x80x9d space (i.e., space unoccupied by tissue or cells). Hollow fiber and disc designs have been reported to be 97% xe2x80x9cdeadxe2x80x9d space8 96% xe2x80x9cdeadxe2x80x9d space14, respectively. In these configurations, the ratio of the dead space to the islet volume is xe2x89xa725. In the optimal bioartificial implant, this ratio should be much smaller. In the limiting case, the implant would be pure tissue.
As a result of imperfect coating, it is possible that islets may protrude from finished capsules, leading to fibrosis48. Another consequence of imperfect coating can be sensitization followed by antibody production, leading to complement lysis.
Defects in the capsules have been reported to lead to fibrotic overgrowth49. Some methods do not appear to be reproducible50.
The optimal bioartificial implant fabrication method should be reproducible and have a high yield. The optimal bioartificial implant should have a small volume ratio and no cells protruding, and be free of physical imperfections that lead to fibrosis.
The optimal bioartificial implant favors the health of the implanted cells. For instance, good glycemia helps all islet implants. It has been demonstrated that islets retain more of their original mass following implantation when the glycemic level of the host is maintained near normal as the islets are engrafting51. It is therefore not surprising that clinical researchers report greater success when efforts were taken to stabilize islet implant recipients"" blood sugar levels52.
A number of reports suggest methods to improve islet cell mass, viability and functionality by including substances in the bioartificial implant composition. Given the importance of oxygen in maintaining cell viability, it is not surprising that there is a report that hemoglobin improves oxygen transport and thus islet viability18. Collagen also has a reported benefit to islet viability, presumably because islets are attachment-dependent cells7. Other components of the extracellular matrix including fibronectin, laminin, and tenascin are also recognized as playing a role in cell growth and differentiation53, and thus may be sustaining.
Numerous trophic hormones and factors have appeared in the literature, including such trophic factors as insulin-like growth factor-I, insulin-like growth factor-II, transforming growth factor-alpha, hepatocyte growth factor/scatter factor, platelet-derived growth factor, and ilotropin, a paracrine/autocrine factor associated with islet differentiation.54,52 There is a report that antioxidant vitamins reduce fibrotic overgrowth55, and another that the vitamin nicotinamide helps islet viability56.
Another approach to maintaining cell viability and functionality is to co-culture with cells that secrete trophic factors57.
The optimal bioartificial implant may include all such substances to the extent that they are compatible with other components and are beneficial to the implanted cells.
Although the discussion herein focuses on islets of Langerhans for treatment of diabetes, many uses of cellular implants to treat diseases have been proposed, including treatment of hemophilia, dwarfism, anemia, kidney failure, anemia, chronic pain, Alzheimer""s disease, fulminant hepatic failure, Parkinson""s disease, etc. This topic has been reviewed.58.
Numerous bioartificial implants have been described. The following discussion is limited to passive diffusion type implants each containing multiple islets, and does not include individually encapsulated islets or vascular devices. (Two examples or capsules are included in the table for purposes of comparison.) In many cases dimensions and tissue density are not reported in the reference, and we have noted the assumptions used to generate numbers in the summary table at the end of the section. Oxygen at the center of the implant has been measured very rarely; oxygen levels were determined by applying the analysis of Colton at al.5
General reviews of immunoisolation technologies were noted earlier; discussions of planar congifurationsxe2x80x94slabs, discs and sheetsxe2x80x94have also been published. For the most comprehensive and detailed on older research, see Scharp59, and for the most recent work, see the two reviews by Colton4,5.
Aebischer et al.60 have described a tubular polymer implant made by xe2x80x9ccoextruding an aqueous cell suspension and a polymeric solution through a common port to form a tubular extrudate having a polymeric outer coating which encapsulates the cell suspension.xe2x80x9d In one embodiment, the tubular extrudate is sealed at intervals to define separate compartments connected by polymeric links. This system has a low cell density, reported at 0.1% in the patent example. The dimensions of the cylinder device do not permit oxygen to reach the center.
Andersson et al.61 describe a laminated double membrane disc designed to simultaneously prevent cellular invasion and promote vascularization. The paper describes fibroblast invasion suggesting a lack of biocompatibility. While tissue density is high and the thickness is sufficiently small to permit oxygen throughout the device, the small diameter of the disc results in insufficient volume per transplant. The design does not appear to permit sufficient control over thickness if the diameter is larger.
Ash et al.62 have described a system comprising a bundle of fibers that remains under the skin allowing replacement of cells. The dimensions of the sack-like device do not permit oxygen to reach the center if cell density is greater than 10%.
Aung et al.24 have described a biohybrid artificial pancreas utilizing mesh-reinforced polyvinyl alcohol hydrogel tubes as membranes. The tubes have a 2 mm ID, and the membrane is 200 xcexcm thick. The configuration prevents suitable kinetics and oxygen tension. As Aung""s group reported33,
xe2x80x9c. . . islets tend to aggregate into large clumps, and subsequent central necrosis occurs, probably due to the hypoxia of the central portion, resulting in impairment or loss of function of the islets within 1 to 2 weeks.xe2x80x9d
Thus, experimental results confirm that the thickness of the tube produces anoxia at the center.
Bae et al.64 describe an implantable and refillable biohybrid artificial pancreas. The configuration is a disc shaped pouch. The polymer (a cellulose acetate coated membrane) is not biocompatible. The dimensions of the disc device do not permit oxygen to reach the center if cell density is greater than 10%.
In a study that measured oxygen tensions in an acrylic tube implant, Bodziony16 found that the amount of oxygen present is too low to support viability of islets. The amount of oxygen present was calculated to be depleted by islet metabolism in less than three minutes.
Gaskill65 proposed a passive diffusion xe2x80x9cintravascular artificial organ comprised of a flexible, hollow, semipermeable catheter containing living cells or tissue.xe2x80x9d It is now known that the proposed materials induce thrombosis when placed in flowing blood. Although dimensions are not disclosed, a tube with sufficiently small diameter to permit oxygen diffusion to the center would be several meters long, much longer than one shown in FIG. 1 of the patent. Thus the invention of Gaskill does not have dimentions allowing oxygen to reach the center if cell density is greater than 10%.
Inoue et al.25 constructed a tube of polyvinyl alcohol membrane. The dimensions of the cylinder device do not permit oxygen to reach the center if cell density is greater than 10%.
Jordan66 describes a sack/tube, and even says that xe2x80x9cthe length of the shortest diffusion path between the interior side of the container wall and the center of the glandular tissue must not be longer on the average than two millimeters.xe2x80x9d However this length is not correct based on current understanding of oxygen diffusion through tissue, and it is also incorrect to neglect the effects of diffusion through the container wall. The Jordan design would have no oxygen in its center if cell density is greater than 10% due to its dimensions.
66Jordan, G. P. W., Artificial gland. U.S. Pat. No. 3,093,831 (1963)
Kopchick et al.67 use hollow fibers seeded with genetically engineered cells to deliver bovine growth hormone. The dimensions of the cylinder device do not permit oxygen to reach the center if cell density is greater than 10%.
67Kopchick, J. J., Leung, F. C., Livelli, T. J., and Malavarca, R. H., Encapsulated mouse cells transformed with avian retrovirus-bovine growth hormone DNA, and a method of administering bgh in vivo; administer by hollow fiber filled with recombinant mouse cell suspension; lactation. U.S. Pat. No. 4,686,098 (1987).
Lacy et al.8 studied hollow fibers fabricated from an acrylic copolymer encapsulating small numbers of rat islets immobilized in an alginate hydrogel. The dimensions of the cylinder device do not permit oxygen to reach the center if cell density is greater than 10%.
8Lacy, P. E., Hegre, O. D., Gerasimidi-Vazeou, A., Gentile, F. T., and Dionne, K. E., Maintenance of Normoglycemia in Diabetic Mice by Subcutaneous Xenografts of Encapsulated Islets. Science, 1991. 254: p. 1782-1784.
Lanza et al.68 used Amicon XM-50 membrane tubes sealed at the ends. The dimensions of the cylinder device do not permit oxygen to reach the center if cell density is greater than 10%.
68Lanza, R. P., Borland, K. M., Lodge, P., Carretta, M., Sullivan, S. J., Muller, T. E., Solomon, B. A., Maki, T., Monaco, A. P., and Chick, W. L., Treatment of severely diabetic pancreatectomized dogs using a diffusion-based hybrid pancreas. Diabetes, 1992. 41(7): p. 886-9.
Lanza, R. P., Sullivan, S. J., and Chick, W. L., Perspectives in Diabetes: Islet transplantation with immunoisolation. Diabetes, 1992. 41: p. 1503-10.
Laue et al.54 studied a regenerated cellulose hollow fiber system. The dimensions of the cylinder device do not permit oxygen to reach the center if cell density is greater than 10%.
54Miettinen, P. J., Otonkoski, T., and Voutilainen, R., Insulin-like growth factor-II and transforming growth factor-alpha in developing human fetal pancreatic islets. J Endocrinol, 1993. 138(1): p. 127-36.
Loeb69 describes an xe2x80x9cartificial endocrine gland for supplying a hormone to a patient including an implantable housing placed in the body and having an impermeable extracorpeal segment and a semipermeable subcutaneous segment [with a] replaceable envelope containing live hormone-producing cells such as pancreatic islet cells.xe2x80x9d Although dimensions are not disclosed, a tube with sufficiently small diameter to permit oxygen diffusion to the center would be many meters long, much longer than one shown in FIG. 8 of the patent. Thus the invention of Loeb does not have dimentions allowing oxygen to reach the center if cell density is greater than 10%.
69Loeb, M. P., Artificial endocrine gland containing hormone-producing cells. U.S. Pat. No. 4,378,016 (1983).
Ohgawara et al.55 describe a diffusion chamber, but dimensions are not given. A cell density of 2% is described.
55Laue, C., Zimmermann, U., Biesalski, H. K., Beyer, J., and Schrezenmeir, J., Antioxidative vitamin reduce fibrous tissue overgrowth of the bioartificial pancreas. Transplant Proc, 1995 27(2): p. 1875-6.
Penfornis et al.70 also made use of the Amicon XM50 hollow fiber described by Lanza. The dimensions of the cylinder device do.not permit oxygen to reach the center if cell density is greater than 10%.
70Penfornis, F., Icard, P., Gotheil, C., Boillot, J., Cornec, C., Barrat, F., Altman, J. J., and Cochin, J. V., Bioartificial pancreas in pigs. Horm Metab Res Suppl, 1990. 25(2): p. 200-2.
Scharp et al.11 studied hollow fibers fabricated from an acrylic copolymer. Human islets were macroencapsulated and allotransplanted subcutaneously. Recipients were patients with type I or type II diabetes and normal control subjects; none was immunosuppressed. The dimensions of the cylinder device do not permit oxygen to reach the center if cell density is greater than 10%.
11Scharp, D. W., Swanson, C. J., Olack, B. J., Latta, P. P., Hegre, O. D., Doherty, E. J., Gentile, F. T., Flavin, K. S., Ansara, M. F., and Lacy, P. E., Protection of encapsulated human islets implanted without immunosuppression in patients with type I or type II diabetes and in nondiabetic control subjects. Diabetes, 1994. 43(9): p. 1167-70. Performed under investigator FDA IND (BB-IND 5103).
Scharp has also developed planar diffusion chambers which have been described by others (see table).
Schrezenmeir et al.18 used regenerated cellulose capillary membranes. The principal object of the study was to show that hemoglobin helped maintain viability by conducting oxygen. The dimensions of the cylinder device do not permit oxygen to reach the center if cell density is greater than 10% in spite of the hemoglobin.
18Schrezenmeir, J., Kirchgessner, J., Gero, L., Kunz, L. A., Beyer, J., and Mueller-Klieser, W., Effect of microencapsulation on oxygen distribution in islets organs. Transplantation, 1994. 57(9): p. 1308-14.
Tze et al.71 investigated polysulfone fibers in a coil configuration, and found massive fibrosis in only a few days. The dimensions of the device do not permit oxygen to reach the center if cell density is greater than 10% center.
71Tze, W. J., Cheung, S. S., Tai, J., Bissada, N., Tsang, A., and Yep, W., Prolongation of pig islet xenograft survival in polysulfone fiber coil. Transplant Proc, 1994. 26(6): p. 3510-1.
Yang et al.14 used agarose to fabricate transplants in microbead, rod and slab configurations.
14Yang, H., Iwata, H., Shimizu, H., Takagi, T., Tsuji, T., and Ito, F., Comparative studies of in vitro and in vivo function of three different shaped bioartificial pancreases made of agarose hydrogel. Biomaterials, 1994. 15(2): p. 113-20.
Various kinds of bioartificial pancreas (BAP) have been developed in the past. There have been many disputes about the advantages and disadvantages of each BAP. However, little attention has been paid to the shape of the devices. In this study, three different shaped BAPs were made of the same material, agarose hydrogel. These are microbead-, rod-and disc-shaped BAPs, which are comparable to microcapsules, hollow fibre diffusion chambers and disc-shaped diffusion chambers, respectively, in shape. Numerical analyses showed that insulin release kinetics depended greatly on the thickness of the gel membrane but not on the shape of the agarose hydrogel. These results suggest that the shape of the BAPs determines the in vivo functioning period of the BAPs and that the microbead is the most suitable shape for the BAP. The authors reported that xe2x80x9csmall differences such as oxygen tension and nutrients supply drastically affect the fate of encapsulated islets.xe2x80x9d Theoretical modeling shows that the dimensions of all three implants do not permit oxygen to reach the center if cell density is greater than 10%.
The following table summarizes prior approaches, giving several quantities for comparison:
total volume per implant is given in cubic millimeters (xcexcl); the volume is determined for the entire transplant including membranes as well as core tissue density is given as a percent of the total volume;
assuming an islet diameter of 150 xcexcm when islet number is given or assuming 2xc3x97108 cells per xcexcl when cell number is given oxygen is determined at the center of the implant furthest from the surface; using measurements (when available) or the equations of Colton et al.5 assuming 10% cell density retrievability, whether the implant(s) can easily be removed
5Colton, C. K., Implantable Biohybrid Artificial Organs. Cell Transplant, 1995. 4(4): p. 415-436.
Prior to the present invention, no bioartificial implant was both (1) small enough in linear dimention to allow effective passive oxygen diffusion into medium density tissue and (2) large enough in volume to contain over 200 islets.
NOTES
1. London, N. J., Robertson, G. S., Chadwick, D. R., Johnson, P. R., James, R. F., and Bell, P. R., Human pancreatic islet isolation and transplantation. Clin Transplant, 1994. 8(5): p. 421-59.
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3. Clayton, H. A., James, R. F., and London, N. J., Islet microencapsulation: a review. Acta Diabetol, 1993. 30(4): p. 181-9 .
4. Colton, C. K. and Avgoustiniatos, E. S., Bioengineering in development of the hybrid artificial pancreas. J Biomech Eng, 1991. 113(2): p. 152-70.
5. Colton, C. K., Implantable Biohybrid Artificial Organs. Cell Transplant, 1995. 4(4): p. 415-436.
6. de Vos, P., Wolters, G., Fritschy, W., and Van Schiltgarde, R., Obstacles in the application of microencapsulation in islet transplantation. Int J Artif Organs, 1993. 16: p. 205-212.
Reach, G., Artificial and bioartificial replacement of the endocrine pancreas. Artif Organs, 1992. 16(1): p. 61-70.
Reach, G., Bioartificial pancreas. Transplant Proc, 1994. 26(2): p. 397-8.
Vanholder, R. and Ringoir, S., Bioartificial pancreas and liver: a review [editorial]. Int J Artif Organs, 1991. 14(7): p. 398-402.
7. Jain, K., Yang, H., Cai, B. R., Haque, B., Hurvitz, A. I., Diehl, C., Miyata, T., Smith, B. H., Stenzel, K., Suthanthiran, M., and et, a., Retrievable, replaceable, macroencapsulated pancreatic islet xenografts. Long-term engraftment without immunosuppression. Transplantation, 1995. 59(3): p. 319-24.
8. Lacy, P. E., Hegre, O. D., Gerasimidi-Vazeou, A., Gentile, F. T., and Dionne, K. E., Maintenance of Normoglycemia in Diabetic Mice by Subcutaneous Xenografts of Encapsulated Islets. Science, 1991. 254: p. 1782-1784.
9. Lacy, P. E., Treating Diabetes with Transplanted Cells. Scientific American No. 273 (1995)
10. Kessler, D. A., Siegel, J. P., Noguchi, P. D., Zoon, K. C., Feiden, K. L., and Woodcock, J., Regulation of Somatic-cell Therapy and Gene Therapy by the Food and Drug Administration. N Eng J Med, 1993. 329: p. 1169-73.
Noguchi, P. D., Cell Transplantation and Federal Regulation. Cell Transplant, 1995. 4(4): p. 411-414. xe2x80x9cIt also seems quite clear that when the source material of organs and tissues in nonhuman, for example of porcine origin, FDA oversight will be involved.xe2x80x9d
11. Scharp, D. W., Swanson, C. J., Olack, B. J., Latta, P. P., Hegre, O. D., Doherty, E. J., Gentile, F. T., Flavin, K. S., Ansara, M. F., and Lacy, P. E., Protection of encapsulated human islets implanted without immunosuppression in patients with type I or type II diabetes and in nondiabetic control subjects. Diabetes, 1994. 43(9): p. 1167-70. Performed under investigator FDA IND (BB-IND 5103).
12. In reference 8, hypoglycemia during GTT was disclosed in the question period following presentation of this paper.
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Horcher, A., Zekorn, T., Siebers, U., Bretzel, R., Zimmermann, U., and Federlin, K., Insulin release from different models of a bioartificial pancreas (Microencapsulation vs. Macroencapsulation vs. Alcinate Coatina). Cell Transplantation, 1992. 1(⅔): p. 175.
14. Yang, H., Iwata, H., Shimizu, H., Takagi, T., Tsuji, T., and Ito, F., Comparative studies of in vitro and in vivo function of three different shaped bioartificial pancreases made of agarose hydrogel. Biomaterials, 1994. 15(2): p. 113-20.
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17. Gero, L., Kirchgessner, J., Kunz, L.A., Mueller-Klieser, W., Laue, C., and Schrezenmeir, J., PO2-gradients in islated piscine islets: effect of fluid convection and barium-alginate encapsulation. Cell Transportation, 1992. 1(2/3): p. 165.
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39. Wahoff, D. C., Stephanian, E., Gores, P. F., Soon-Shiong P., Hower, C., Lioveras, J. K., and Sutherland, D. E., Intraperitoneal transplantation of microencapsulated canine islet allografts with short-term, low-dose cyclosporine for treatment of pancreatectomy-induced diabetes in dogs. Transplant Proc, 1994. 26(2): p. 804.
40. Lamberton, R. P., and Lipsky, M. H., Neovascularization; sponge surrounding ligated blood vessel and semipermeable cell container. U.S. Pat. No. 4,699,141 (1987)
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42. Dalmasso, A. P., The complement system in xenotransplantation. Immunopharmacology, 1992. 24(2): p. 149-60.
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44. Hamelmann, W., Gray, D. W., Cairns, T. D., Ozasa, T., Ferguson, D. J., Cahill, A., Welsh, K. I., and Morris, P. J., Immediate destruction of xenogeneic islets in primate model. Transplantation, 1994. 58(10): p. 1109-14.
45. Zekorn, T., Entenmann, H., Horcher, A., Siebers, U., Klock, G., Zimmermann, U., Federlin, K., and Bretzel, R. G., Lymphoid activation by micro- and macroencapsulated islets during mixed lymphocyte islet culture. Acta Diabetol, 1993. 30(4): p. 238-42.
46. Grohn, P., Klock, G., Schmitt, J., Zimmermann, U., Horcher, a., Bretzel, R. G., Hering, B. J., Brandhorst, D., Brandhorst, H., Zekorn, T., et al., Large-scale production of Ba(2+)xe2x88x92 alginate-coated islets of Langerhans for immunoisolation. Exp Clin Endocrinol, 1994. 102(5): p. 380-7.
47. Horcher, A., Zekorn, T., Siebers, U., Klock, G., Schnettler, R., Arnold, M., Federlin, K., Zimmermann, U., and Bretzel, R. G., Insulin release from different models of a bioartificial pancreas (microencapsulation versus alginate-coating). Transplant Proc, 1992. 24(6): p. 2950-1.
48. de Vos, P., Wolters, G. H., and van Schilfgaarde, R., Possible relationship bewteen fibrotic overgrowth of alginatexe2x80x94polylysine xe2x80x94alginate microencapsulated pancreatic islets and the microcapsule integrity. Transplant Proc, 1994. 26(2): p. 782-3.
49. Siebers, U., Zekorn, T., Bretzel, R. G., Planck, H., Renardy, M., Zschocke, P., and Federlin, K., Histocompatibility of semipermeable membranes for implantable diffusion devices (bioartificial pancreas). Transplant Proc, 1990. 22(2): p. 834-5.
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50. Yderstraede, K. and Starklint, H., Transportation of encapsulated neonatal rat islets to nude mice and NMRI mice using the renal subcapsular space. Abstract from 14th Workshop of the study group Artificial Insulin Delivery Systems, Pancreas and Islet Transportation (AIDSPIT) of the European Association for the Study of Diabetes (EASD). Igls, Austria, Jan. 30-31, 1995. Horm Metab Res, 1995. 27(1): p. 47-66.
51. Juang, J. H., Bonner-Weir, S., Wu, Y. J., and Weir, G. C., Beneficial influence of glycemic control upon the growth and function of transplanted islets. Diabetes, 1994. 43(11): p. 1334-9.
52. Hering, B. J., Browatzki, C. C., Schultz, A. O., Bretzel, R. G., and Federlin, K., Islet Transplant Registry report on adult and fetal islet allografts. Transplant Proc, 1994. 26(2): p. 565-8.
53. Rosenberg, L., In Vivo Cell Transformation: Neogenesis of Beta Cells from Pancreatic Ductal Cells. Cell Transplant, 1995. 4(4): p. 371-383. See page 375.
54. Miettinen, P. J., Otonkoski, T., and Voutilainen, R., Insulin-like growth factor-II and transforming growth factor-alpha in developing human fetal pancreatic islets. J Endocrinol, 1993. 138(1): p. 127-36.
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55. Laue, C., Zimmermann, U., Biesalaki, H. K., Beyer, J., and Schrezenmeir, J., Antioxidative vitamins reduce fibrous tissue overgrowth of the bioartificial pancreas. Transplant Proc, 1995 27(2): p. 1875-6.
56. Ohgawara, H., Miyazaki, J.-i., Karibe, S., Tashiro, F., Akaike, T., and Hashimoto, Y., Embedded-culture of Pancreatic beta-cells derived from transgenic mouse insulinoma as a potential souce for xenotransplantation using a diffusion chamber. Cell Transplant, 1995. 4(3): p. 307-313.
57. Aebischer, P. and Winn, S. R., In vivo delivery of active factors by co-cultured cell implants; semipermeable membranes. U.S. Pat. No. 5,182,111 (1993).
58. Bellamkonda, R. and Aebischer, P., Review: Tissue engineering in the Nervous System. Biotech Bioeng, 1994. 43(543-554).
Colton (note 5) See the introduction dection, especially the second paragraph, and references cited therein.
Lysaght (note 2) Table 1.
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59. Scharp, D. W., Mason, N. S., and Sparks, R. E., Islet Immuno-isolation: the use hybrid artificial organs to prevent islet tissue rejection. World J Surg, 1984, 8: p. 221-229.
60. Aebischer, P., and Wahlberg, L., Method of encapsulating cells in a tubular extrudate; coextrusion of semipermeable polymeric memebrane and cells. U.S. Pat. No. 5,284,761 (1994). For the comparison table, we estimated the tube diameter and length from the figures and discussion (column 5, lines 15-17). Tissue density is based on 1xc3x97105 cells/ml reported in the patent (column 8, line 10) compared with packed tissue density of 2 to 5 xc3x97108 cells/ml.
61. Andersson, A., Eizirik, D. L., Hellerstrom, C., Johnson, R. C., and Pipeleers, D. G., Morphology of encapsulated human pancreatic islets transplanted into nude mice. Transplant Proc, 1994. 26(2): p. 802-3. The core of this device is high density packed islets reenforced with polyester fibers. The overall density and thickness of the device are determined assuming that the core is 0.12 mm thick and the two laminated double membranes are 0.08 mm thick.
62. Ash, S. R. and Loeb, M. P., Body cavity access device containing a hormone source. U.S. Pat. No. 4,402,694 (1983). For the comparison table, we estimated the tube diameter and length from the figures and discussion (column 5, lines 3 and 12; claim 12). Tissue density is not reported.
63. Aung, T., Inoue, K., Kogire, M., Sumi, S., Fujisato, T., Gu, Y. J., Shinohara, S., Hayashi, H., Doi, R., Imamura, M., et al., Improved insulin release from bioartificial pancreas using mesh-reinforced polyvinyl alcohol hydrogel tube: immobilization of islets in agarose gel.
64. Bae, Y. H. and Kim, S. W., Implantable and refillable biohybrid artificial pancreas; for use in the treatment of diabetes. U.S. Pat. No. 5,262,055 (1993). The thickness is calculated from numbers in Example 5 and the assumption that 80% of the surface is channels, and the membranes are each 0.05 mm thick.
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The present invention concerns a bioartificial implant and methods for its manufacture and use. The dimensions of the bioartificial implant are such that cell viability may be maintained by passive diffusion of nutrients, and preferably, such that a high cell density can be maintained. The dimensions of the bioartificial implant are also such that the bioartificial implant is macroscopic and is easily retrievable from the host and is large enough to contain a significant fraction of the tissue required to achieve the desired therapeutic effect. The permeability of the bioartificial implant is such that cell viability may be maintained by passive diffusion of nutrients, and preferably such that passive diffusion of secreted cell products permits rapid response to changing physiological conditions. At the same time, the permeability of the membrane sufficiently impedes diffusion of antibody and complement to prevent lysis of the implanted cells, even when the tissue is a xenograft. The bioartificial implant is biocompatible, meaning it produces no foreign body reaction.
The dimensions of the present bioartificial implant, when in a thin sheet configuration, are such that the surface area of a side of a sheet is at least 30 mm2, preferably at least 2.5 cm2 and more preferably 10 cm2, as defined by either (a) the diameter (if the sheet is circular) or (b) the area determined by the method of converging polygons. Although the maximum dimensions can be that which is tolerated by the patient into whom the implant is placed, for ease of fabrication and economy of implanted cells, the maximum surface area of a side of the present thin sheet implant may be 400 cm2, more preferably 300 cm2 and most preferably 250 cm2 (for a human patient).
In the present bioartificial implant, the cell density is that which can be contained within a thin alginate gel coat. Preferably, the cell density is at least 10%, more preferably 20% and most preferably at least 35% by volume.
The surface of the bioartificial implant is biocompatible. We have found that attempts to induce neovascularization at the surface of the implant with synthetic polymers60,3 are less than ideal for long term implant viability. We have found that implants that are neutral (causing neither fibrosis nor neovascularization) have been shown to last over a year with minimal decay of function12.
60. Aebischer, P. and Wahlberg, L., Method of encapsulating cells in a tubular extrudate; coextrusion of semipermeable polymeric membrane and cells. U.S. Pat. No. 5,284,761 (1994). For the comparison table, we estimated the tube diameter and length from the figures and discussion (column 6, lines 15-17). Tissue density is based on 1xc3x97105 cells/ml reported in the patent (column 8, line 10) compared with packed tissue density of 2 to 5 xc3x97108 cells/ml). 3. Clayton, H. A., James, R. F., and London, N. J., Islet microencapsulation: a review. Acta Diabetol, 1993. 30(4): p. 181-9 . 12. In reference 8, hypoglycemia during GTT was disclosed in the question period following presentation of this paper.
The bioartificial implant is described using the terms xe2x80x9ccord,xe2x80x9d xe2x80x9ccoatxe2x80x9d and xe2x80x9covercoat.xe2x80x9d The core comprises the living tissue, trophic factors and nurse cells, alginate polymer crosslinked with a multivalent cation such as calcium, and a fiber mesh for strength. The coat comprises alginate polymer crosslinked with a multivalent cation that serves to control permeability. The overcoat comprises alginate polymer crosslinked with a multivalent cation that serves to render the bioartificial implant biocompatible.
One aspect of the present invention is its shape or configuration. Previous inventions have responded to inherent limitations on diffusion of oxygen by lowering cell densities within the bioartificial implant. We have found that an effective implant must have medium to high tissue densities to minimize the volume of the total bioartificial implant, and that the thickness of a sheet or slab must be very small to permit effective oxygen diffusion. The sum of the core, coat and overcoat thicknesses should be less than 400 xcexcm, preferably 350 xcexcm or less, and more preferably no more than 300 xcexcm. The coat and overcoat thickness should be minimized so that the tissue quantity may be maximized. We have found that the coat and overcoat thicknesses may be from 10 to 100 xcexcm thick, preferably from 10-80 xcexcm, and most preferably from 10-50 xcexcm. Biocompatible implant coat thicknesses of only tens of xcexcm have never been before reported. The length and width of the bioartificial implant on the other hand should be maximized to permit the greatest possible volume of living tissue to be included in the bioartificial implant and to permit easy retrieval.
Another aspect of the present invention is the material out of which the bioartificial implant is constructed. Biocompatible purified alginates have been described, but have only been used to produce coated and encapsulated implants. No bioartificial implant has been described using alginate in a thin sheet. The properties of alginate gel can be controlled by selecting the G and M content, the chain length, the alginate concentration, and counterions (e.g. calcium, zinc, barium or a combination thereof). Alginate in the core is compatible with living tissue. The fabrication of alginate hydrogels is compatible with cell viability. Sodium alginate used to fabricate the core can be mixed with tropic factors and nurse cells along with the secreting tissue before gelation with multivalent cations to provide a supportive environment. Alginate for the coating can be selected as to chain length and G and M fractions and be gelled with various multivalent cations to control the permeability of the coat. Alginate for the overcoat can be selected so as to maximize the biocompatibility of the bioartificial implant.
The bioartificial implant is fabricated using a series of molds constructed with frit materials that can be molded or milled, and membranes. This allows diffusion of chelating agents (e.g., sodium citrate) or multivalent cation gelling agents (e.g., calcium, barium or zinc chlorides) to liquify and gel, respectively, the core, coat and overcoat. The manufacturing process makes use only of ions known to be compatible with the implanted cells.
Although many variations of the method exist, the essence of the process is simple. The shape of the core, coat and overcoat are molded while the alginate is liquid. The core and coat (and later the coat and overcoat) are crosslinked by simply contacting liquid alginate containing a small amount of chelating agent to the gelled layer. The chelating agent diffuses into the gelled layer and partially liquifies it. When a cationic crosslinking agent is subsequently added, a tight bond is formed between the layers. The outer surface is made very smooth through the simple step of wetting the mold with crosslinking agent solution before contacting the mold with the liquid coat or overcoat. We have found that contact with the membrane thus wetted immediately produces a very smooth surface.
Because the coat and overcoat are fabricated from liquids, they can be made very thin, even as thin as a few xcexcm.
We have invented a bioartificial implant of dimensions never before achieved, with many attendant advantages. For example, one object of the present invention is to provide a bioartificial implant that is easily retrievable from the host.
Another object of the present invention is to provide a bioartificial implant in a thin sheet configuration permitting both high tissue densities and diffusion to the tissue cells of the amounts of nutrients, oxygen and other substances required for cellular health, longevity and effective function after implantation.
Another object of the present invention is to provide a bioartificial implant in an easily retrievable thin sheet configuration, permitting both high tissue densities and effective diffusion of nutrients into and cellular products out from the implant.
Another object of the present invention is to provide a bioartificial implant in the configuration of a thin sheet of viable, physiologically active, tissue cells for implantation which is physiologically acceptable to the host and which effectively provides prolonged protection of the tissue cells, after implantation, from destruction by the host immune system.
Another object of the present invention is to provide an effective implant coating material in a retrievable thin sheet configuration which is physiologically acceptable, non-fibrogenic and non-toxic to host tissue.
Another object of the present invention is to provide a bioartificial implant containing trophics such as nurse cells, ground substances, nutrients, hormones or oxygen carriers to support the cellular health, longevity and effective function of the implant after implantation.
A further object of the present invention is to provide a novel manufacturing process for effectively enclosing an implant (e.g., cells, tissues and/or other biological substances) with a barrier or membrane which is physiologically acceptable, non-fibrogenic and non-toxic to host tissue, which may provide a complete barrier coating with a controlled thickness and controlled permeability to intermediately sized proteins, and which is easily retrievable.
In summary, the present invention may comprise an implant core having a thin sheet configuration comprising viable, physiologically active, tissue cells and a crosslinked alginate gel and optionally, trophic factors and nurse cells, and optionally, a fiber mesh support. The alginates are preferably free from fibrogenic concentrations of impurities.
The bioartificial implant may have a coat and overcoat to control permeability and enhance biocompatibility. The implant sheet is thin and may be permeable enough to provide a physiologically acceptable oxygen tension at the center of the sheet when implanted in a suitable site in a human or animal subject. The thinness and permeability of the implant allows diffusion of nutrients, oxygen, metabolic waste products and secreted tissue products. The implant preferably inhibits diffusion of antibody and complement.
Preferably, the coat permits rapid diffusion of substances below 50 Kd and significantly inhibits diffusion of substances over 100 kD. The coat is also very thin, preferably approximately 10-50 xcexcm. The coat may comprise and thus, be constructed with, for instance, short chain, high M alginate gelled with a mixture of calcium and zinc ions.
Suitable cells for the present implant include, for example, pancreatic islets, renal cortex cells, parathyroid cells, thyroid cells, adrenal cells, hepatic cells, cells of various origins that have been genetically engineered to secrete useful substances, cells of various origins that have been genetically engineered to metabolize harmful substances, tissues, and the like.
The process of the present invention for making a biocompatible implant may comprise the steps of:
(a) forming a core containing viable, physiologically active, tissue donor cells in an alginate gel, preferably in a thin, sheet-shaped mold and more preferably by crosslinking an alginate solution containing the cells;
(b) contacting the core with a second alginate solution containing a concentration of citrate sufficient to induce at least partial liquification of the alginate gel in the core;
(c) crosslinking the second alginate solution and liquified alginate gel in the core to form a coat layer bonded to the core, and thus, the biocompatible implant, preferably by diffusing a crosslinking agent into the second alginate solution and liquified alginate gel in the core.
Optionally, crosslinking step (c) may comprise contacting the inner surface of the mold with an aqueous calcium ion solution to create a smooth outer surface on the biocompatible implant. This optional step may be performed in addition to the diffusing step. A further option is to repeat step (b) with a third alginate solution containing sufficient citrate to induce at least partial liquification of the alginate gel in the coat, and repeat step (c) by crosslinking the third alginate solution and liquified alginate gel in the coat to form an overcoat layer bonded to the coat. The coat of the biocompatible implant may be formed to control permeability, and the overcoat formed to enhance biocompatibility.

RETRIEVABLE BIOARTIFICIAL IMPLANTS HAVING DIMENSIONS ALLOWING RAPID DIFFUSION OF OXYGEN AND RAPID BIOLOGICAL RESPONSE TO PHYSIOLOGICAL CHANGE, PROCESSES FOR THEIR MANUFACTURE, AND METHODS FOR THEIR USE


A light sensitive display.

The present invention relates to touch sensitive displays.
Touch sensitive screens ("touch screens") are devices that typically mount over a display such as a cathode ray tube. With a touch screen, a user can select from options displayed on the display's viewing surface by touching the surface adjacent to the desired option, or, in some designs, touching the option directly. Common techniques employed in these devices for detecting the location of a touch include mechanical buttons, crossed beams of infrared light, acoustic surface waves, capacitance sensing, and resistive materials.
For example, Kasday, U.S. Pat. No. 4,484,179 discloses an optically-based touch screen comprising a flexible clear membrane supported above a glass screen whose edges are fitted with photodiodes. When the membrane is flexed into contact with the screen by a touch, light which previously would have passed through the membrane and glass screen is trapped between the screen surfaces by total internal reflection. This trapped light travels to the edge of the glass screen where it is detected by the photodiodes which produce a corresponding output signal. The touch position is determined by coordinating the position of the CRT raster beam with the timing of the output signals from the several photodiodes. The optically-based touch screen increases the expense of the display, and increases the complexity of the display.
Denlinger, U.S. Pat. No. 4,782,328 on the other hand, relies on reflection of ambient light from the actual touch source, such as a finger or pointer, into a pair of photosensors mounted at corners of the touch screen. By measuring the intensity of the reflected light received by each photosensor, a computer calculates the location of the touch source with reference to the screen. The inclusion of the photosensors and associated computer increases the expense of the display, and increases the complexity of the display.
May, U.S. Pat. No. 5,105,186, discloses a liquid crystal touch screen that includes an upper glass sheet and a lower glass sheet separated by spacers. Sandwiched between the glass sheets is a thin layer of liquid crystal material. The inner surface of each piece of glass is coated with a transparent, conductive layer of metal oxide. Affixed to the outer surface of the upper glass sheet is an upper polarizer which comprises the display's viewing surface. Affixed to the outer surface of glass sheet is a lower polarizer. Forming the back surface of the liquid crystal display is a transflector adjacent to the lower polarizer. A transflector transmits some of the light striking its surface and reflects some light. Adjacent to transflector is a light detecting array of light dependent resistors whose resistance varies with the intensity of light detected. The resistance increases as the light intensity decreases, such as occurs when a shadow is cast on the viewing surface. The light detecting array detect a change in the light transmitted through the transflector caused by a touching of viewing surface. Similar to touch sensitive structures affixed to the front of the liquid crystal stack, the light sensitive material affixed to the rear of the liquid crystal stack similarly pose potential problems limiting contrast of the display, increasing the expense of the display, and increasing the complexity of the display.
Touch screens that have a transparent surface which mounts between the user and the display's viewing surface have several drawbacks. For example, the transparent surface, and other layers between the liquid crystal material and the transparent surface may result in multiple reflections which decreases the display's contrast and produces glare. Moreover, adding an additional touch panel to the display increases the manufacturing expense of the display and increases the complexity of the display. Also, the incorporation of the touch screen reduces the overall manufacturing yield of the display.
Accordingly, what is desired is a touch screen that does not significantly decrease the contrast ratio, does not significantly increase the glare, does not significantly increase the expense of the display, and does not significantly increase the complexity of the display.
The foregoing and other objectives, features, and advantages of the invention will be more readily understood upon consideration of the following detailed description of the invention, taken in conjunction with the accompanying drawings.

Abstract: A light sensitive display.


An in-line programming (ILP) system and method for programming and testing programmable integrated circuit devices (PICs) and performing the assembly of printed circuit board assemblies (PCBAs). Printed circuit boards enter and leave the ILP system on a conveyor system. PICs are loaded into the ILP system, and the ILP system automatically programs and tests the PICs and places them onto the PCBs as the PCBs arrive on the conveyor. The programming and testing operations are performed by the same piece of equipment that performs the PCBA assembly operation.

The present invention generally relates to concurrent automated programming of programmable electronic devices, and more particularly to programming and testing multiple device types and patterns and performing circuit board assembly simultaneously in a single in-line programming device.
In the semiconductor industry, a considerable number of electronic devices such as programmable integrated circuit (PIC) devices are provided by vendors in programmable form with blank memories or unspecified connections between arrays of logic. Users can then custom configure or program the electronic devices to perform their intended function by programming them, transferring or xe2x80x9cburning inxe2x80x9d a sequence of operating codes into the memory, or by specifying a particular arrangement of gating logic connections.
Numerous manufacturers have developed automated machinery for handling and programming such devices. Such machinery moves blank devices from a source medium (e.g., trays, tubes, tape) to one or more programming sites, carries out the programming operation on each device, and moves programmed devices from the programming sites to an output medium (e.g., trays, tubes, tape). Typical users of automated programming equipment are highly sensitive to system throughput, which is typically measured in correctly programmed devices per hour, and yield, which is typically defined as the percentage of devices which are correctly programmed.
Before any printed circuit board assembly (PCBA) containing a programmable integrated circuit (PIC) can be used, the PIC must be configured, or programmed, so that it may perform its intended function. During programming, a pattern is loaded into the unprogrammed PIC. These patterns may be changed from time to time as the requirements of the function of the PCBA change over time. Also, in some applications, the pattern may be individualized for each PCBA that is assembled.
For years, PICs have been programmed before being assembled onto a printed circuit board using a methodology called off-line programming (OLP). This, however, created some problems in that OLP of the PICs has to be performed prior to assembly. Specialized equipment must also be obtained to perform OLP. Further, OLP has to be scheduled, which may delay the manufacture of PCBAs and create scheduling problems and bottlenecks in the process. Moreover, once the PICs are programmed, they must be stored until the assembly process begins. This storage and related delay typically creates an inventory of programmed PICs. Not only does this inventory cost money, but in the event that a pattern change is required immediately, the inventory of programmed PICs may have to be destroyed, which adds to the cost and creates an additional delay before the assembly of more PCBAs can commence.
To solve these problems, a technique called in-circuit programming (ICP) was developed. ICP allows for a PIC to be programmed after it is placed on a printed circuit board, i.e., after the PCBA is assembled. Thus, the need for an inventory of programmed devices was eliminated, and individualized PICs no longer needed to be matched with the corresponding PCBA because all the PICs are identical (unprogrammed) at assembly time.
However, new problems arose. For example, because it is not feasible to program all PICs in circuit, the designers of the PCBA must choose only devices that are ICP compatible. ICP compatible PICs cost more than similar non-ICP compatible PICs in many cases, so the cost of the PCBA may be higher when using ICP. Additionally, the PCBA design may be more complex to accommodate ICP, so the time to market may be negatively impacted. Furthermore, specialized equipment is required, and software must be written, to perform the programming operation, which also may impact time to market for the PCBA. Since the programming operation may take a number of minutes to perform, a production line may be slowed down waiting for programming to complete. To address this throughput problem, some users may set up several ICP programming stations to service a single PCBA assembly line. However, this solution requires additional equipment, floor space in the factory and capital outlay. Additionally, if the application for the PCBA requires that the PICs be programmed with individualized patterns, it may be necessary to match the individual PICs with their corresponding individual PCBAs. This additional complication adds additional cost and complexity to the assembly operation. Finally, in the event that the PIC fails to program, the entire PCBA will have to be reworked to replace the PIC.
Accordingly, what is needed in the art is a system and methodology for programming PICs and assembling PCBAs without the drawbacks associated with the off-line programming and in-circuit programming techniques.
Briefly, the invention provides in-line programming techniques for programming and testing any combination of devices and patterns. The techniques of the present invention are useful for programming a variety of types of programmable integrated circuit devices (PICs), including for example, flash memories, EEPROMs, microcontrollers, PLDs, PALs, FPGAs and the like. According to the invention, an in-line programming (ILP) system programs and tests PICs and performs the assembly of printed circuit board assemblies (PCBAs). Printed circuit boards enter and leave the ILP system on a conveyor system. PICs are loaded into the ILP system, and the ILP system automatically programs and tests the PICs and places them onto the PCBs as the PCBs arrive on the conveyor.
The present invention addresses all of the above problems (e.g., costs, complications and delays) by performing the programming and testing operations with the same piece of equipment that performs the assembly operation. Using the techniques of the present invention, PICs are programmed on demand so the need for an inventory of programmed PICs is eliminated, and changes to the program pattern may be incorporated immediately without waste. Any PICs that fail to program are rejected by the ILP system so that bad PICs are never placed onto a PCBA. Because the PCBA does not have to be designed to accommodate an in-circuit programming technique, the PCBA designer is unconstrained in choice of PICs. The ILP system generally programs PICs faster than PICs can be programmed using the in-circuit programming methodology. The ILP system is also able to program a number of devices simultaneously, allowing a PCBA assembly line to produce PCBAs at a faster pace than that at which a single PIC can be programmed. Thus, an assembly line incorporating an ILP system may be smaller and produce PCBAs faster, with higher quality and less expense than an assembly line incorporating an in-circuit programming system. Further, the use of an ILP system in an assembly line allows for PCBAs to be produced less expensively than in an assembly line incorporating programmed PICs from an off-line programming system.
According to an aspect of the present invention, a method of automatically assembling a printed circuit board assembly (PCBA) in an assembly apparatus is provided. The method typically comprises the steps of a) receiving, in the assembly apparatus, a programmable electronic device to be programmed, and b) automatically programming the electronic device in the assembly apparatus. The method also typically includes the steps of c) receiving a printed circuit board in the assembly apparatus, and d) assembling the PCBA in the assembly apparatus by automatically placing the programmed electronic device on the printed circuit board so as to form the PCBA.
According to another aspect of the present invention, an assembly apparatus capable of automatically assembling a printed circuit board assembly (PCBA) is provided. The apparatus typically comprises a means for receiving, in the assembly apparatus, a programmable electronic device to be programmed, and a means for automatically programming the electronic device in the assembly apparatus. The apparatus also typically includes a means for receiving a printed circuit board in the assembly apparatus, and a means for automatically placing the programmed electronic device on the printed circuit board so as to form the PCBA.
Reference to the remaining portions of the specification, including the drawings and claims, will realize other features and advantages of the present invention. Further features and advantages of the present invention, as well as the structure and operation of various embodiments of the present invention, are described in detail below with respect to the accompanying drawings. In the drawings, like reference numbers indicate identical or functionally similar elements.

Method of programming a programmable electronic device by an in-line programming system